Tissue ablation system with energy distribution

ABSTRACT

A microwave ablation system includes an energy source adapted to generate microwave energy and a power splitting device having an input adapted to connect to the energy source and a plurality of outputs. The plurality of outputs are configured to be coupled to a corresponding plurality of energy delivery devices. The power splitting device is configured to selectively divide energy provided from the energy source between the plurality of energy devices.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a continuation of U.S. patent application Ser. No. 15/005,479, filed on Jan. 25, 2016, which is a continuation of U.S. patent application Ser. No. 14/691,710, filed on Apr. 21, 2015, now U.S. Pat. No. 9,375,278, which is a continuation of U.S. patent application Ser. No. 12/562,842, filed on Sep. 28, 2009, now U.S. Pat. No. 9,095,359, the entire contents of each of which are incorporated by reference herein.

BACKGROUND

1. Technical Field

The present disclosure relates to apparatus and methods for providing energy to tissue and, more particularly, to devices and electromagnetic radiation delivery procedures utilizing ablation probes and methods of controlling the delivery of electromagnetic radiation to tissue.

2. Discussion of Related Art

Treatment of certain diseases requires destruction of malignant tumors. Electromagnetic radiation can be used to heat and destroy tumor cells. Treatment may involve inserting ablation probes into tissues where cancerous tumors have been identified. Once the probes are positioned, electromagnetic energy is passed through the probes into surrounding tissue.

In the treatment of diseases such as cancer, certain types of cancer cells have been found to denature at elevated temperatures that are slightly lower than temperatures normally injurious to healthy cells. Known treatment methods, such as hyperthermia therapy, use electromagnetic radiation to heat diseased cells to temperatures above 41° C. while maintaining adjacent healthy cells below the temperature at which irreversible cell destruction occurs. These methods involve applying electromagnetic radiation to heat, ablate and/or coagulate tissue. Microwave energy is sometimes utilized to perform these methods. Other procedures utilizing electromagnetic radiation to heat tissue also include coagulation, cutting and/or ablation of tissue.

Electrosurgical devices utilizing electromagnetic radiation have been developed for a variety of uses and applications. A number of devices are available that can be used to provide high bursts of energy for short periods of time to achieve cutting and coagulative effects on various tissues. There are a number of different types of apparatus that can be used to perform ablation procedures. Typically, microwave apparatus for use in ablation procedures include a microwave generator, which functions as an energy source, and a microwave surgical instrument having an antenna assembly for directing the energy to the target tissue. The microwave generator and surgical instrument are typically operatively coupled by a cable assembly having a plurality of conductors for transmitting microwave energy from the generator to the instrument, and for communicating control, feedback and identification signals between the instrument and the generator.

Microwave energy is typically applied via antenna assemblies that can penetrate tissue. Several types of antenna assemblies are known, such as monopole and dipole antenna assemblies. In monopole and dipole antenna assemblies, microwave energy generally radiates perpendicularly away from the axis of the conductor. A monopole antenna assembly includes a single, elongated conductor that transmits microwave energy. A typical dipole antenna assembly has two elongated conductors, which are linearly aligned and positioned end-to-end relative to one another with an electrical insulator placed therebetween. Each conductor may be about ¼ of the length of a wavelength of the microwave energy, making the aggregate length of the two conductors about ½ of the wavelength of the supplied microwave energy. During certain procedures, it can be difficult to assess the extent to which the microwave energy will radiate into the surrounding tissue, making it difficult to determine the area or volume of surrounding tissue that will be ablated.

SUMMARY

According to an embodiment of the present disclosure, a microwave ablation system includes an energy source adapted to generate microwave energy and a power splitting device having an input adapted to connect to the energy source and a plurality of outputs. The plurality of outputs are configured to be coupled to a corresponding plurality of energy delivery devices. The power splitting device is configured to selectively divide energy provided from the energy source between the plurality of energy devices.

According to another embodiment of the present disclosure, a microwave ablation system includes an energy source adapted to generate microwave energy and a power splitting device having an input adapted to connect to the energy source and a plurality of outputs. The plurality of outputs are configured to be coupled to a corresponding plurality of energy delivery devices via corresponding transmission lines. The power splitting device is configured to selectively divide energy provided from the energy source between the plurality of energy delivery devices either equally or unequally.

According to another embodiment of the present disclosure, a method for providing energy to a target tissue includes the steps of positioning a plurality of energy delivery devices into a portion of the target tissue and selectively dividing energy on a plurality of channels to at least one of the energy delivery devices. The method also includes applying energy from one or more of the energy delivery devices to the target tissue.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic diagram of an electrosurgical system for treating tissue, according to an embodiment of the present disclosure;

FIG. 2 is a schematic diagram of an electrosurgical system for treating tissue, according to one embodiment of the present disclosure;

FIG. 3 is a schematic diagram of an electrosurgical system for treating tissue, according to another embodiment of the present disclosure;

FIG. 4 is a schematic diagram of an electrosurgical system for treating tissue, according to another embodiment of the present disclosure; and

FIG. 5 is a block diagram illustrating a method for treating tissue, according to an embodiment of the present disclosure.

DETAILED DESCRIPTION

Hereinafter, embodiments of the presently disclosed tissue ablation systems are described with reference to the accompanying drawings. Like reference numerals may refer to similar or identical elements throughout the description of the figures. As used herein, the term “microwave” generally refers to electromagnetic waves in the frequency range of 300 megahertz (MHz) (3×108 cycles/second) to 300 gigahertz (GHz) (3×1011 cycles/second). As used herein, the phrase “transmission line” generally refers to any transmission medium that can be used for the propagation of signals from one point to another.

Various embodiments of the present disclosure provide electrosurgical systems for treating tissue and methods of controlling the delivery of electromagnetic radiation to tissue. Embodiments may be implemented using electromagnetic radiation at microwave frequencies or at other frequencies. Electrosurgical systems for treating tissue, according to various embodiments of the present disclosure, deliver microwave power to a plurality of electrosurgical devices. Electrosurgical devices, such as ablation probes, for implementing embodiments of the present disclosure may be inserted directly into tissue, inserted through a lumen, such as a vein, needle or catheter, placed into the body during surgery by a clinician, or positioned in the body by other suitable methods known in the art.

FIG. 1 is a schematic diagram of an electrosurgical system for treating tissue, according to one embodiment of the present disclosure. Referring to FIG. 1, the electrosurgical system 100 includes an electrosurgical generator 120 for generating an output signal, a power splitter 150 coupled to the electrosurgical generator 120, and an electrosurgical instrument or device 130 coupled to the power splitter 150. The power splitter 150 is coupled to a transmission line 107 that electrically connects the power splitter 150 to an output 124 on the electrosurgical generator 120. The device 130 includes an antenna assembly 132 for delivery of electromagnetic radiation, coupled to a transmission line 104 that electrically connects the antenna assembly 132 to the power splitter 150. Although not shown as such in FIG. 1, device 130 may include a plurality of antenna assemblies.

The electrosurgical generator 120 may include other input or output devices such as knobs, dials, switches, buttons, graphical user interfaces, displays, and the like for control, indication and/or operation. The electrosurgical generator 120 may be capable of generating a plurality of output signals of various frequencies that are input to the power splitter 150. In one embodiment, the electrosurgical generator 120 generates a plurality of microwave signals at substantially the same frequency. The electrosurgical generator 120 may include a control unit (not shown) that controls operations of the electrosurgical generator 120, such as time of operation, power output and/or the mode of electrosurgical operation, which may have been selected by the clinician.

The electrosurgical system 100 may include a footswitch (not shown) coupled to the electrosurgical generator 120. When actuated, the footswitch causes the electrosurgical generator 120 to generate microwave energy. The device 130 may include knobs, dials, switches, buttons or the like (not shown) to communicate to the electrosurgical generator 120 to adjust or select from a number of configuration options for delivering energy. Utilizing knobs, dials, switches or buttons on the device 130 and/or a footswitch enables the clinician to activate the electrosurgical generator 120 to energize the device 130 while remaining near the patient P regardless of the location of the electrosurgical generator 102.

Although not shown as such in FIG. 1, electrosurgical system 100 may include a plurality of channels defined by a plurality of electrosurgical devices and a plurality of transmission lines that electrically connect the electrosurgical devices to the power splitter 150. In an embodiment, the power splitter 150 is capable of monitoring the phase of each channel and adjusting the phase of the signal in each channel with respect to the other channel(s) to a predetermined phase relationship. The power splitter 150 provides a plurality of signals to the device 130 in a set of phase relationships between the signals. Although the power splitter 150 is illustrated as a standalone module in FIG. 1, it is to be understood that the power splitter 150 may be integrated fully or partially into the electrosurgical generator 120, the device 130, and/or other devices.

The antenna assembly 132 includes multiple antennas and/or multiple antenna elements, each driven by an output signal of the power splitter 150. The antenna assembly 132 may also include multiple antenna circuits, each driven by an output signal of the power splitter 150.

In embodiments, the antenna assembly 132 is a microwave antenna configured to allow direct insertion or penetration into tissue of the patient P. The antenna assembly 132 may be axially rigid to allow for tissue penetration. The antenna assembly 132 is sufficiently small in diameter to be minimally invasive of the body, which may reduce the preparation of the patient P as might be required for more invasive penetration of the body. The antenna assembly 132 is inserted directly into tissue, inserted through a lumen, such as, for example, a vein, needle or catheter, placed into the body during surgery by a clinician, or positioned in the body by other suitable methods.

FIG. 2 is a schematic diagram of an electrosurgical system for treating tissue, according to another embodiment of the present disclosure. Referring to FIG. 2, the electrosurgical system 200 includes a microwave signal source 210 providing a microwave frequency output signal to a microwave amplifier unit 220, a microwave power splitter 230 coupled to the microwave amplifier unit 220, and a first, a second and a third microwave ablation antenna assembly 270A, 270B and 270C, each coupled to the microwave power splitter 230. The microwave signal source 210 is capable of generating a plurality of output signals of various frequencies that are input to the microwave amplifier unit 220. The microwave amplifier unit 220 may have any suitable input power and output power.

In the electrosurgical system 200, a first transmission line 250A electrically connects the first antenna assembly 270A to the microwave power splitter 230, defining a first channel; a second transmission line 250B electrically connects the second antenna assembly 270B to the microwave power splitter 230, defining a second channel; and a third transmission line 250C electrically connects the third antenna assembly 270C to the microwave power splitter 230, defining a third channel. The first, second and third transmission lines 250A, 250B and 250C may each include one or more electrically conductive elements, such as electrically conductive wires.

In an embodiment, the first, second, and third transmission lines 250A, 250B and 250C each have substantially the same length, which preserves the phase relationship between the electrical signals in each channel of the electrosurgical system 200. It is to be understood that “length” may refer to electrical length or physical length. In general, electrical length is an expression of the length of a transmission medium in terms of the wavelength of a signal propagating within the medium. Electrical length is normally expressed in terms of wavelength, radius, or degrees. For example, electrical length may be expressed as a multiple or sub-multiple of the wavelength of an electromagnetic wave or electrical signal propagating within a transmission medium. The wavelength may be expressed in radians or in artificial units of angular measure, such as degrees. The microwave power splitter 230 may be implemented by any suitable power divider that provides equal or unequal power split at the output ports of the microwave power splitter 230 while substantially maintaining phase and amplitude balance. For example, the microwave power splitter 230 may be implemented using a 3-way power divider that provides equal or unequal power split at its output ports while maintaining a phase balance of <+/−45 degrees.

Each antenna assembly 270A, 270B and 270C typically includes a plurality of electrodes disposed on a rigid or bendable needle or needle-like structure. The antenna assemblies 270A, 270B and 270C are positioned substantially parallel to each other, for example, spaced about 5 millimeters (mm) apart, and inserted directly into tissue or placed into the body during surgery by a clinician, or positioned in the body by other suitable methods. Although the electrosurgical system 200 illustrated in FIG. 2 includes three microwave ablation antenna assemblies 270A, 270B and 270C, it is to be understood that any “N” number of antenna assemblies may be utilized and that microwave power splitter 230 may be implemented by any suitable power divider that divides or splits a microwave input signal into “N” number of output signals of equal or unequal power.

The electrosurgical system 200 delivers microwave power to one or more antenna assemblies 270A, 270B and 270C of the three-channel system. The electrosurgical system 200 may deliver substantially in-phase microwave power to each antenna assembly 270A, 270B and 270C. By controlling the phase of ablation probes with respect to each other, according to embodiments of the present disclosure, a desired effect on tissue between the probes is produced. In a resection procedure where a long thin ablation line is desired, probes that are 180 degrees out of phase with respect to each other produce a desired effect on tissue. In ablation procedures using in-phase probes, according to various embodiments of the present disclosure, there may be a reduction in energy that might otherwise move between the antenna shafts toward the surface with out-of-phase probes.

In an embodiment, the electrosurgical system 200 is implemented with operating frequencies in the range of about 915 MHz to about 5 GHz, which may be useful in performing ablation procedures and/or other procedures. It is to be understood that the electrosurgical system 200 may be implemented with any appropriate range of operating frequencies.

In another embodiment, the electrosurgical system 200 delivers microwave power to particular channels individually or any combination of one or more channels equally or unequally. The microwave signal source 210 and/or antenna assembly 270A, 270B and 270C may include input or output devices such as knobs, dials, switches, buttons, graphical user interfaces, displays, and the like to facilitate selective activation of energy delivery to particular channels or combination of channels. For example, a user may select channels to which energy is delivered. In this scenario, if the second and third channels are selected, energy delivery may be divided equally (e.g., P/2) between the second and third channels and, thus, unequally between the first channel and the second and third channels since no energy is delivered to the first channel in this scenario. Further, in this scenario, energy may be delivered to individual channels according to selected time intervals by dynamically changing the channels to which energy is delivered. For example, energy may be delivered to the first channel at a time interval t1. At a subsequent time interval t2, energy is delivered to the first channel and the third channel. At a subsequent time interval t3, energy delivery to the first channel is stopped and energy delivery to the third channel continues. At a subsequent time interval t4, energy delivery to all channels is stopped.

In another embodiment, the microwave power splitter 230 divides energy between the antenna assemblies 270A, 270B and 270C to tailor the size and shape of ablation lesions. With this purpose in mind, electrosurgical system 200 may include a suitable storage device (not shown) integrated within the microwave signal source 210, the microwave power splitter 230, or be a stand-alone device, that is configured to store settings or data corresponding to particular ablation geometries (e.g., ablation images, antenna tip geometries, power division settings, power amplitude settings, etc.). Based on the stored settings or data, the microwave signal source 210 modifies delivery of microwave power to the microwave power splitter 230 and/or the microwave power splitter 230 modifies the division of microwave power between the channels to achieve the desired ablation geometry.

FIG. 3 is a schematic diagram of an electrosurgical system for treating tissue, according to an embodiment of the present disclosure. Referring to FIG. 3, the electrosurgical system 300 includes a microwave signal source 310 providing a microwave frequency output signal to a microwave power splitter 330, and a first, a second, a third, and a fourth microwave ablation antenna assembly 370A, 370B, 370C, and 370C, each coupled to the microwave power splitter 330. The microwave signal source 310 is capable of generating a plurality of output signals of various frequencies that are input to the microwave power splitter 330.

The microwave power splitter 330 includes a first quarter wavelength transmission line 350A that electrically connects the first antenna assembly 370A to the microwave signal source 310, defining a first channel; a second quarter wavelength transmission line 350B that electrically connects the second antenna assembly 370B to the microwave signal source 310, defining a second channel; a third quarter wavelength transmission line 350C that electrically connects the third antenna assembly 370C to the microwave signal source 310, defining a third channel; and a fourth transmission line 350D that electrically connects the fourth antenna assembly 370D to the microwave signal source 310, defining a fourth channel. Transmission lines 350A, 350B, 350C, and 350D each include one or more electrically conductive elements, such as electrically conductive wires. In an embodiment, transmission lines 350A, 350B, 350C, and 350D each have substantially the same length, which preserves the phase relationship between electrical signals in each channel of the electrosurgical system 300.

As is known in the art, for maximum power transfer between a power source (e.g., microwave signal source 310) and a load (e.g., antenna assemblies 370A, 370B, 370C, 370D), the load impedance must be equal to the source impedance. For the case wherein the transmission line between the power source and the load is quarter wavelength, as described with reference to the embodiment of FIG. 3, an impedance of the microwave signal source 310 is calculated using the following equation (1):

Z _(in) =Z _(o) ² /Z _(L)  (1)

In equation (1), Z_(in) is the input impedance to the quarter wavelength transmission lines 350A, 350B, 350C, and 350D (e.g., the impedance at the microwave signal generator 310), Z_(o) is the characteristic impedance of the quarter wavelength transmission lines 350A, 350B, 350C, and 350D (e.g., the impedance at the microwave power splitter 330), and Z_(L) is the impedance of the antenna assemblies 370A, 370B, 370C, 370D. Applying equation (1) to the illustrated embodiment of FIG. 3, yields the following equation (2) to account for the four inputs to the quarter wavelength transmission lines 350A, 350B, 350C, and 350D:

4*Z _(in) =Z _(o) ² /Z _(L)  (2)

Since Z_(L) must equal Z_(in) to achieve maximum power transfer, as discussed hereinabove, solving for the characteristic impedance Z_(o) of the quarter wavelength transmission line yields the following equation (3):

Z _(o)=2*Z _(in)  (3)

By way of example, given that Z_(L)=Z_(in)=50 ohms, the characteristic impedance Z_(o) of the transmission lines 350A, 350B, 350C, and 350D is equal to 100 ohms, and the electrical length of the transmission lines 350A, 350B, 350C, and 350D is set to a quarter wavelength, the load impedance Z_(L) of the antenna assemblies 370A, 370B, 370C, 370D at the input of the power splitter 330 is transformed from 50 ohms, which corresponds to a full wavelength, to 200 ohms, which corresponds to a quarter wavelength (i.e., 50 ohms/0.25=200 ohms). Since the four antenna assemblies 370A, 370B, 370C, 370D are in parallel with microwave signal generator 310, the equivalent resistance Z_(L) of the antenna assemblies 370A, 370B, 370C, 370D is equal to 200 ohms divided by four antenna assemblies or 50 ohms. Since Z_(IN)=50 ohms=Z_(L), maximum power transfer will occur between microwave signal generator 310 and each of antenna assemblies 370A, 370B, 370C, 370D.

Although the electrosurgical system 300 illustrated in FIG. 3 includes four microwave ablation antenna assemblies 370A, 370B, 370C, and 370D and four quarter wavelength transmission lines 350A, 350B, 350C, and 350D, it is to be understood that any N number of antenna assemblies and any N number of quarter wavelength transmission lines may be utilized.

FIG. 4 is a schematic diagram of an electrosurgical system 400 for treating tissue, according to another embodiment of the present disclosure. Referring to FIG. 4, the electrosurgical system 400 illustrated is a three-channel system that includes a microwave signal source 410, a microwave amplifier 420, a first, a second, and a third microwave ablation antenna assembly 470A, 470B, and 470C, and a controller 430 that includes one input 432 and a first, a second, and a third output 434A, 434B, and 448C.

The electrosurgical system 400 includes a first transmission line 475A that electrically connects the first antenna assembly 470A to the first output 434A, defining a first channel; a second transmission line 475B that electrically connects the second antenna assembly 470A to the second output 434B, defining a second channel; and a third transmission line 475C that electrically connects the third antenna assembly 470C to the third output 434C, defining a third channel. The first, second, and third transmission lines 475A, 475B, and 475C each include one or more electrically conductive elements, such as electrically conductive wires. In an embodiment, the first, second, and third transmission lines 475A, 475B, and 475C each have substantially the same length, which preserves the phase relationship between electrical signals in each channel of the electrosurgical system 400.

The microwave signal source 410 provides a microwave frequency output signal to the amplifier 420. The microwave amplifier 420 provides an output signal through an output terminal that is electrically coupled to the input 432 of the controller 430. Although the amplifier 420 is illustrated as a standalone module in FIG. 4, it is to be understood that the amplifier 420 may be integrated fully or partially into the controller 430. Controller 430 includes a first output-side directional coupler 465A, a second output-side directional coupler 465B, and a third output-side directional coupler 465C. Output-side directional couplers 465A, 465B, 465C are configured to measure power at each output 434A, 434B, 434C, respectively, and to transmit a microwave signal, received as input, to antenna assemblies 470A, 470B, and 470C.

The controller 430 includes a first isolator 422 electrically coupled between the input 432 and an input-side directional coupler 424. The first isolator 422 operates to appear as a fixed matching load to the microwave signal source 410 to prevent detuning thereof due to variations in load impedance caused by, for example, antenna assemblies 470A, 470B, and 470C and/or transmission lines 475A, 475B, and 475C. The first isolator 422 transmits the microwave signal from the amplifier 420 to the input-side directional coupler 424. The input-side directional coupler 424 measures the microwave signal received from the amplifier 420 as input and transmits the microwave signal to a first switching device 440 electrically coupled thereto. The first switching device 440 transmits the microwave signal to any one or more of a 1:2 power divider 450, a 1:3 power divider 452, and/or a second switching device 442, individually or in any combination thereof.

Upon receiving the microwave signal from switching device 440, power divider 450 divides the microwave signal as output between the second switching device 442 and a third switching device 444. Upon receiving the microwave signal from switching device 440, power divider 452 divides the microwave signal as output between the second switching device 442, the third switching device 444, and the third output-side directional coupler 465C. The third output-side directional coupler 465C powers antenna assembly 470C by transmitting the microwave signal received from power divider 452 to the third output 434C.

Upon receiving the microwave signal from any combination of the first switching device 440, power divider 450, and/or power divider 452, the second switching device 442 transmits the microwave signal to the first output-side directional coupler 465A. The first output-side directional coupler 465A powers antenna assembly 470A by transmitting the microwave signal received from the second switching device 442 to the first output 434A.

Upon receiving the microwave signal from any combination of power divider 450 and/or 452, the third switching device 444 transmits the microwave signal to the second output-side directional coupler 465B. The second output-side directional coupler 465B powers antenna assembly 470B by transmitting the microwave signal received from the third switching device 444 to the second output 434B.

In operation of electrosurgical system 400, depending on the configuration of switching devices 440, 442, and 444, the output power values corresponding to the three outputs 434A, 434B, and 434C for a given power P will be either P, 0, and 0; P/2, P/2, and 0; or P/3, P/3, and P/3.

Controller 430 further includes a first isolator 460A electrically coupled between the second switching device 442 and the first output-side directional coupler 465A; a second isolator 460B electrically coupled between the third switching device 444 and the second output-side directional coupler 465B; and a third isolator 460C electrically coupled between power divider 452 and the third output-side directional coupler 465C. First, second, and third isolators 460A, 460B, and 460C are configured to appear as a fixed matching load to the microwave signal generator 410 to prevent detuning thereof due to variations in load impedance caused by, for example, antenna assemblies 470A, 470B, and 470C and/or transmission lines 475A, 475B, and 475C.

Switching devices 440, 442, 444 may be any suitable switching device configured to output power to a load connected thereto based on more than one inputs such as, for example, a single pole double throw switch (SPDT), a single pole triple throw switch (SP3T), etc.

In embodiments, any one or more of isolator 422 and isolators 460A, 460B, 460C may be a three-port circulator, as is known in the art, having one of its three ports terminated in a fixed matching load to the microwave signal source 410 to effectively operate substantially as described above with reference to isolator 422 and/or isolators 460A, 460B, 460C.

The controller 430 may include one or more phase detectors (not shown) to compare the respective phases of electrical signals inputted through the input 432. By comparing a reference signal, such as a clock signal, to a feedback signal using a phase detector, phase adjustments may be made based on the comparison of the electrical signals inputted, to set the phase relationship between electrical signals in each channel of the electrosurgical system 400.

In an embodiment, the controller 440 delivers phase-controlled microwave power through the outputs 434A, 434B and 434C to the antenna assemblies 470A, 470B and 470C, respectively, irrespective of the phase of the electrical signal inputted through the input 432.

FIG. 5 is a flowchart illustrating a method for providing energy to a target tissue, according to an embodiment of the present disclosure. Referring to FIG. 5, in step 510, a plurality of energy delivery devices are positioned into a portion of the target tissue. The energy delivery devices may be implemented using any suitable electrosurgical instruments or devices, such as, for example, the device 130, according to embodiments of the present disclosure described in connection with FIG. 1.

The energy delivery devices are positioned into a portion of a target site on the tissue or adjacent to a portion of a target site on the tissue. The energy delivery devices are inserted directly into tissue, inserted through a lumen, such as a vein, needle or catheter, placed into the body during surgery by a clinician or positioned in the body by other suitable methods. The energy delivery devices include any suitable antenna assemblies for the delivery of electromagnetic radiation, such as, for example, the antenna assemblies 270A, 270B and 270C, according to embodiments of the present disclosure described in connection with FIG. 2.

In step 520, microwave power is selectively transmitted on a plurality of channels to any one or more of the energy delivery devices. The microwave power may be transmitted to the energy delivery devices from the microwave power splitter 230, according to embodiments of the present disclosure described in connection with FIG. 2, the microwave power splitter 330, according to embodiments of the present disclosure described in connection with FIG. 3, or the controller 440, according to embodiments of the present disclosure described in connection with FIG. 4.

In step 530, microwave energy from any one or more energy delivery devices is applied to the target tissue.

While several embodiments of the disclosure have been shown in the drawings, it is not intended that the disclosure be limited thereto, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplifications of particular embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto. 

1-20. (canceled)
 21. An electrosurgical system comprising: an electrosurgical energy source; a controller configured to operably couple to the electrosurgical energy source, the controller including: a plurality of outputs; a power splitting device having an input and a plurality of outputs; and first and second switching devices, wherein: the first switching device includes an input configured to connect to the electrosurgical energy source, a first output connected to the second switching device, and a second output connected to the power splitting device, and the second switching device includes a first input connected to the first output of the first switching device, a second input connected to the power splitting device, and an output connected to one of the plurality of outputs of the controller; and a plurality of energy delivery devices each configured to electrically communicate with one of the plurality of outputs of the controller.
 22. The electrosurgical system according to claim 21, wherein the electrosurgical energy source is a microwave generator configured to generate microwave energy.
 23. The electrosurgical system according to claim 21, wherein each of the plurality of energy delivery devices is a microwave ablation device including an elongated needle structure configured to be inserted through tissue.
 24. The electrosurgical system according to claim 21, wherein the power splitting device is configured to selectively divide electrosurgical energy between the plurality of energy delivery devices.
 25. The electrosurgical system according to claim 21, wherein the power splitting device is configured to equally divide electrosurgical energy between the plurality of energy delivery devices.
 26. The electrosurgical system according to claim 21, wherein the power splitting device is configured to unequally divide electrosurgical energy between the plurality of energy delivery devices.
 27. The electrosurgical system according to claim 21, wherein the controller is configured to divide output of electrosurgical energy based on a predetermined time interval.
 28. The electrosurgical system according to claim 21, wherein the controller is configured to divide output of electrosurgical energy based on a desired ablation geometry.
 29. The electrosurgical system according to claim 21, further comprising a plurality of transmission lines each interconnecting an output of the plurality of outputs of the power splitting device to a respective energy delivery device of the plurality of energy delivery devices.
 30. The electrosurgical system according to claim 29, wherein each transmission line of the plurality of transmission lines has a length of a quarter wavelength.
 31. A controller configured to couple to an electrosurgical energy source, the controller including: a plurality of outputs; a power splitting device having an input and a plurality of outputs; and first and second switching devices, wherein: the first switching device includes an input configured to connect to the electrosurgical energy source, a first output connected to the second switching device, and a second output connected to the power splitting device, and the second switching device includes a first input connected to the first output of the first switching device, a second input connected to the power splitting device, and an output connected to one of the plurality of outputs of the controller.
 32. The controller according to claim 31, wherein the controller is configured to divide output of electrosurgical energy based on a predetermined time interval.
 33. The controller according to claim 31, wherein the controller is configured to divide output of electrosurgical energy based on a desired ablation geometry. 